DE2238928A1 - VENTILATION DEVICE - Google Patents

Description

PH B. 32166.

. Heinrich Hartmann 2238928 wijn / rv.

Pnfpnlassessor

Applicant: O. PHiLiPS ¹ GlQBlMPiHfmiBB

Act ·, HJB-32.186 voini γ. Aug 1972

"Ventilator".

The invention relates to a time-controlled ventilator Art with a program timer to control a ventilation cycle with an inhalation phase and an exhalation phase, their time periods can be set and with which device per inatinization phase of a ventilation cycle a precisely measured amount of Cas given to a patient can be administered, with a gas container of variable content Measure and temporarily save the above precisely measured ' Amount of gas during an exhalation phase, as well as to drive out de / · exactly measured amount of gas during an inhalation phase, with a drive device to enlarge and reduce the contents of the gas container with regard to the gas metering, storage and expulsion function desseltsr. pit of a display device for displaying the current size of the content of the gas container and with adjusting means !! to adjust the size

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a precisely measured amount of gas.

For a timed ventilator, the duration is the inhalation and exhalation phase adjustable, while with a volume-controlled ventilator a previously determined volume ventilation3-gases is administered to a patient regardless of the ventilation rate.

The gas volume, daa a patient per ventilation cycle

is referred to as the "cycle volume" and the total amount of gas administered per minute to a patient is called the "minute debit", i.e. the cycle volume multiplied by the ventilation rate, expressed in the number of ventilation cycles per minute.

With this type of ventilator, the length of time

the inhalation phase and the exhalation phase, as well as the cycle volume accordingly " set the ventilation needs of the patient beforehand. The duration of the inhalation and exhalation phases is known electronically to control, for example with the help of a program switch that comprises a multivibrator with an adjustable pause time for each of the two states.

The output signals of the multivibrator control solenoids,

which couple the gas flow to and from the patient to the solenoids " Control gas switching valves. Most of these use ventilators one or more bellows, which are filled with ventilation gas during each exhalation phase and which contract and which is stored in this way Volume of gas during the subsequent inhalation phase feed, the expansion and shrinkage of the bellows by the Ργο ^ γηππ timer is controlled.

The minute debit is determined by the extent of expansion and Determines the shrinkage of the bellows or the bellows. Dieo is beispi (lu

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• With the help of sliding stops for the bellows, on the bellows itself or changeable on the bellows drive mechanism.

The drive mechanism is mostly of a mechanical type and includes a pneumatic piston motor.

It is also known to use an electrical switch operated by a. Bellows when stretching is actuated around on this

Wc * ice To avoid further stretching via electronic devices.

Each of the known constructions has the compartment part, aar,? - the required setting action is cumbersome and imprecise. in the

!1 -

in the former case a mechanical transmission is necessary and this shows

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the disadvantage that the transmission is difficult to use, even with Consideration a.if the size of the amount to be generated by the operator Force and also leads to a reduction in accuracy. In the latter In this case, the location of the electrical switch must be changed, each time a different setting of the cycle volume is desired is. This is also cumbersome.

Another disadvantage of the known methods of gas volume adjustment occurs when deep inhalation is required.
During normal ventilation it is necessary to repeatedly use the lungs
of a patient at regular intervals, varying from 1 to 3 minutes, with oinom larger gas volumes and for a longer time than in a normal Janatraungsphase. ·

In the known ventilators, in order to maintain a fine fit, it is necessary to change the settings for the duration of the breathing nose and the cycle volume during a single inhalation phase. Pi s is, as r-rläutert, a cumbersome act, amr particularly given little time available.

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The invention now aims to provide a ventilator of the input! mentioned kind of soaking with an improved adjustability for dat cycle volume and is characterized in that the display device contains a first converter whose output signal in size « • In hatred is for the size of the moment the content "dee Caabehfilters, carrion"

the setting means for setting the size of the precisely measured gas me a »wide converter, whose output signal in size a Maos fttr is the exact amount to be measured per ventilation cycle, that a signal output of the first converter with a first signal input and a signal output of the second converter with a second signal input of a matching arrangement and that a signal output of the comparison arrangement is is coupled to a switch for switching the drive arrangement of the gas container on and off.

With the ventilator according to the invention, the Enlargement of the content of the gas container (for example the abovementioned bellows) the volume is constantly displayed and 'with a electrical signal representative of the desired volume, compared and the final parity signal of the comparison arrangement avoids further increase by ensuring that the for the amount of gas required to ventilate the patient precisely .measured and temporarily stored during the immediately preceding exhalation. The adjustment means for the cycle volume can be on simply consist of a potentiometer, which is arranged in an arbitrary but ergonomically appropriate place on the control panel of the device and with a hint of Zyklugvolune calibrated setting scale can be provided. It's not a mechanical one Transmission required and the adjustment knob of the potentiometer IBsst *

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operate in a simple way and can use the ergonomically correct Place to be arranged.

One embodiment of the invention has the mark on that the device comprises a second comparison arrangement, the signal output of the first converter with a first signal input of the comparison arrangement and a second signal input of the same is coupled to a signal output of an adjustment arrangement, with the aid of which an output signal can be set to match the output of the first Converter - corresponds if the gas container is in the. Condition of minimal Content is located. The converter for displaying the gas container content is on also used in this way to indicate that the entire cycle volume has been delivered from the container to the patient during inhalation, D.a.W. that the bellows has returned to the minimum level.

An AusfUhrungsbeispiel the invention is in the drawings and is described in more detail below. Show it:

1 shows a schematic representation of a ventilation circuit.

2 shows the circuit diagram of the electronic control arrangement,

J shows a multivibrator which has an advantage in the circuit arrangement can be used according to Fig. 2,

4 shows the circuit diagram of a so-called deep breathing unit.

“The arrangement of Figure 1 includes two through a solenoid

actuated gas control valves S and S _t which are shown in the usual symbolic form, the right part representing the solenoid, while the zigzag line to the left indicates that the solenoid is reset by a spring, while the left block continues the Passage _# for the gas shows with the solenoid at rest and the right block

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represents this passage with the solenoid in working condition, im Working state the left block is replaced by the right block. Feed openings of these valves are at the inlet DG with a source of Propellant under pressure, for example compressed air, connected. In the figure are the lines for propellant gas as simple lines and the lines ftlr the ventilation gas shown as double lines.

ti

The openings 1 and 1 ^{1 of} the valves S and S "are with the

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Propellant gas source DG and the openings 2 and 2 ¹ with openings of a pneuaatisoh operated drive motor D. connected, which has a cylinder and a

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Flask contains, while openings 3 and 3 ¹ with the atmosphere A.

bundθη are, if necessary via non-illustrated silencers.

The ventilation device contains on the inhalation side

a ventilation inlet RG for Cas (for example pure air), under atmospheric pressure, check valves 11HV ₁ and NHV ₂ , an inhalation valve IV, which is operated by the solenoid DS ₁ , bellows B. and B ₂ , which move under the influence of the pneumatic motor DC, expand and shrink, and a voltage regulator FRC (for example an adjustable constriction). On the exhalation side, gas from the patient flows through the exhalation valve EV, a volumetric _{meter VM 1} which measures the volume of the gas originating from the patient, and a check valve NRV. into the atmosphere ^ at).

S. The solenoid valve is switched on during the inhalation phase and the solenoid valve S "during at least a portion of the Ausatnungsphase. Control circuits for these solenoids are described below.

The circuit arrangement shown is fairly common

and the operation is as follows. First of all, it is assumed that valve S is switched on and that bellows B and B _{2 are} required with> lem

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union volume of the ventilation gas to be administered externally to the patient are filled. The propellant gas is supplied from the inlet BG. Via the gates 1 and 2 of the {opened, th) valve S. _{supplied to the upper space of the cylinder of the motor BC 1} , whereby the piston and the piston rod are driven waiting, so that the bellows are compressed and the ventilation gas contained therein is expelled the same is driven out. The solenoid BS ₁ is excited simultaneously with the valve S ₁ and opens the inhalation valve IV. The ventilation gas is now under the influence of the pressure of the propellant gas at a rate and in an amount that is determined by the setting of the flow regulator PHC driven by the bellows, the dp.s check valve IiRVp opens and flows through the hose HL ₁ to the bifurcation Y of the face mask or the ventilation tube. A (not shown) safety

The valve SV _1, which prevents the build-up of excess pressure in the airways, can be arranged in the ventilation air line shown. A suitable safety valve is described in the applicant's application PHB 32188. The pressure in the inhalation air line keeps the check valve NRV ₁ closed because this pressure is higher than the atmospheric pressure of the ventilation gas on the other side of the valve.

During the inhalation side, the exhalation valve EV

held closed by the solenoid DS "which solenoid is energized during the inhalation time. This ensures that no ventilation gas can escape through the exhalation line. A way by which that out of the non-driving spaces of the motor DC. Driven gas can escape during the movement of the piston in question, leads through the gate 20 in the cylinder and the (non-opened) valve S ₂ into the atmosphere.

At the end of the inhalation time, valve S ₁ becomes ineffective.

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and the valve S "effective. In this state, the opening 20 of the manure DC ₁ propellant gas is supplied, while a Entltiftungsweg in the atmosphere via the opening 10 and the (non-effective) valve S ₁ lit.

The upward movement of the piston of motor DC ₁ causes the pressure in bellows B. and B _{2 to be} reduced, thereby releasing the check valve NRV. opened and breathing gas is sucked through the inlet RG into the bellows. The inhalation valve IV is closed by the solenoid DS ₁ and the exhalation valve EV is opened by the fact that the solenoid DSp is now moved upwards by the associated spring

The pressure in the patient's lungs is higher than that

atmospheric pressure, so that the check valve NRV_ is closed and that Non-return valve NRV, which opens the gas in the lungs of the Patient via the Y fork, the HL- hose, the exhalation valve EV (open), the volume meter VM and the check valve KBV. (opened) can escape into the atmosphere.

During the exhalation time, bellows B ₁ and B.

filled with ventilation gas to the required volume for one breath is saved to the patient during the next inspiratory period to be administered.

According to the invention, the bellows are provided with a displacement transducer VR. This is represented in the form of a potentiometer, whose sliding contact is operated by the bellows. A fixed DC voltage is applied to the outer terminals of the potentiometer VR. created and the output signal SS is taken from the sliding contact in the manner shown; this output signal is a DC voltage signal, the is proportional to the position of the bellows and consequently to the content of the bellows

The way in which this signal is used to convey the content of the

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Bellows and in this way the volume of gas required for one breath to be measured exactly up to a given value! is based on of Fig. 2, which is a block diagram of the electronic " Control circuit of a ventilator according to the invention.

A program timer with a known type of multivibrator MV, which is shown in detail in FIG. 3, is used to program the inhalation and exhalation phases and the control resistors are shown as potentiometers VE ₇₅ and VR calibrated in time units and on the Main control panel of the ventilation device arranged. The potentiometer VR. to display the contents of the bellows, which indicates the height of the bellows and consequently the volume of the gas present therein in the manner described above, gives an analog signal at a first input of a first comparison circuit CCL. The potentiometer VR_ is the converter for setting the precisely measured breathing gas quantity and outputs an analog signal, etc. ^ ke the required volume in the bellows is "on the second input of the comparator CO .. the Auβgangssignal the comparison circuit is supplied via an amplifier to an input of a UN-gate _G?, the other input of which is the exhalation signal from the multivibrator MV

of the AND gate G _? is fed via a signal amplifier A. and an inverting power amplifier A _{2 to} ^the exhalation valve S ₂ , which has been described above with reference to FIG. The exhalation signal of the multivibrator MV is fed to the inhalation valve S via a signal amplifier A and an inverting power amplifier A.

It is assumed that the multivibrator is in the for

Inhalation phase belonging state is switched so that it is a logical one There is a "1" at the inhalation output and a logical "0" at the exhalation output.

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The "1 ¹¹ at the input of Ver3tSrkers A, occurs as" 0 "(ground) at the valve S ₁ and sets this out of service. The at one input of the AND Toree G occurring" O "-Auegangssignal the multivibrator has the appearance of a "0" as the input of amplifier A. result, and thus the occurrence of a "1" on the valve S _0, which therefore remains ineffective. in this way, the valve S ₁ is set in operation and, as based on during this phase 1, the bellows B ₁ - B_ are drawn together and ventilation gas is supplied to the patient.

At the end of the inhalation phase, the duration of which is determined by the setting of the potentiometer VH, the multivibrator switches to the state that corresponds to the exhalation phase, so that the output signals are reversed. The valve S ₁ is therefore no longer. -Excited and the valve S "is put into operation via the gate G_, at the upper input of which a" 1 "occurs which is transmitted via the amplifier Aj. originates from the comparison arrangement CO _1. The comparison _{arrangement Cf) 1} is of a known type and supplies an output signal "1" until the two input signals become equal, whereupon the output signal changes to a "0". In this way, as already mentioned, a "1" occurs at the two inputs of the AND gate G_, so that a "0" occurs at valve S-, which then becomes effective.

The fact that the solenoid of valve S is no longer energized and the solenoid of valve S ₂ is activated has the consequence that the ventilation circuit switches to the breathing phase and the bellows expand. The signal appearing at the upper input of the comparator CO ^ potential decreases in this manner always continues to increase, until it reaches the value that has been previously set with the Gasvolumenpotentiometer VR, _# at which time determines the comparison circuit one R equality of Eingangseignale and Auegangssignal of a "1" into a

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• Ό "changes. This blocks the AND gate Gg so that the solenoid of the Y-valve S _{2 is} no longer excited and the bellows B ₁ -B_ cannot expand any further *. The bellows only contain the ventilation gas volume required for one breath, such as this has been determined beforehand by setting the gas volume potentiometer VR ₂ .

The gate G. iat an analog gate »that of the volume potentiometer VR _? The resulting signal is unchanged, unless: a blocking signal "1" is fed to the lower input via line &. The tasks of the lines ti, b., £, d_, e_ and f_ are described below.

By using an electronic display transducer to display the contents of the bellows, an advantageous property can be easily obtained. If, for example, the air line is at least partially blocked at a certain point between the container for breathing gas, which is formed by the bellows B ₁ and B ₂ , and the patient, the reduction in gas flow can lead to the fact that during the inhalation phase not the full volume necessary for one breath is delivered to the patient. -In this way, the bellows will not flow completely empty during this time. -According to an advantageous embodiment of the invention, the fact that the display transducer VR. is used not only to indicate the volume required for a breath, but also to indicate the empty condition of the bellows, which will give an alarm signal when a blockage occurs.

For this purpose, the output signal of the potentiometer VH ₁ in

Converter CO with the one resulting from a preset potentiometer VRj Signal compared which potentiometer to the empty state of the bellows set iat. This preset regulation will be used during the first earth test

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set the ventilator and is not indicated on the Sohaltpult · The Auegangeeignal the comparator arrangement CO ₂ is supplied via an AND gate G. the input of a monostable multivibrator with a time setting MS ₁ * of a known type. The output of the monostable multivibrator supplies an alarm signal which, in the embodiment in question, is used to ignite a lamp, but the alarm arrangement can of course also have another form.

As long as the bellows contain gas, the input signals for the balancing arrangement C0_ are unequal, so that it is an output signal Returns "1". This output signal "1" keeps the amplifier A, the AND gate G, in an effective state, as long as the bellows are not empty or at least are in a state of minimal content. At the end of the inhalation phase, the Bellows have supplied the amount of gas required for one breath to the patient and have reached the state of minimal content. The comparison ■ o hold C0_ determines this state and the output signal changes to • ine "1", whereby "the gate G. is blocked. If the bellows at the end of the Inhalation phase their contents are not released, the gate G- remains locked. That

• N

Output signal "0", which occurs in the transition to the exhalation phase at the inhalation output of the multivibrator MV, is dlffere: adorned by the capacitor C, so that a brief ^M 0 "pulse is produced at the lower input of the gate G_, which gate then has an output ^H returns 0 ^H -Inpuls. this short pulse triggert.den monostable multivibrator MS., which is then triggered during the unstable period of for example 1 second, after which it returns to the stable state. in this way, during one second in the transition from the Inhalation phase in an Ausatsungsphaee an alarm signal-given to make someone aware that it is you

Errors there.

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Using fundamental principle thereof of a comparison, a further advantageous feature, in another embodiment of the invention are provided and that a possibility of a so-called "patient trigger," is well known, can convulsive _# try to inhale a patient during an expiration phase of the respirator, and the purpose of this exemplary ' Guide form is to recognize any such thing immediately and to switch the ventilator from exhaling to inhaling in order to help the patient in his attempt to inhale in this way. A third comparison arrangement is CO _{3 for this purpose} . provided, the output signal _{of which is fed via an inverting amplifier A 7 to} a further monostable alarm trigger MÖ_ and to the part for the exhalation phase of the multivibx ators K7.

A signal occurs at the input PM of the comparison arrangement CO on, which comes from a (not shown) pressure gauge that the Monitors pressure in the lungs and provides an analog output signal that is proportional to this pressure. Such a pressure gauge is described in the applicant's patent application PHB 32208. A patient trigger potentiometer VR, - iat previously set to a value, - the one in centimeter water column expressed negative pressure value and which is adapted to the patient to be ventilated, the setting on a ■ The scale below the setting button ^ on the control panel can be read »If the patient tries to inhale during an exhalation phase, the Pressure in the air line to a negative value. If this is through the The value detected by the pressure gauge supplies a signal to the input PH which the previously with the help of the potentiometer VR, - corresponds to the adjusted value the comparison arrangement CO is effective and supplies an output signal "1".

This is converted into an "O" -SignaX by the inverting amplifier A _7.

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converts, so that the monostable multivibrator MS is triggered and activated Gives an alarm signal with a fixed duration, in the same way as with the mono-stable multivibrator MS. the case is. The signal "0" is also supplied to the exhalation part of the multivibrator MV and causes this immediately switches to the inhalation phase and in this way the patient helps in his attempt to inhale.

As can be seen, normal and inverting amplifiers are used in the logic circuit of the embodiment described. These amplifiers are shown because they are practical Embodiment used diode-transistor logic (DTL), with amplifier required are. How self-evident can be a other logic can be used, e.g. TTL, in which case the amplifiers are not necessary. Furthermore, a logic with opposite polarity can of course also be used, with the gates correspondingly be changed. All of these possibilities are known to a person skilled in the art and the invention therefore need not be viewed in such a way that it is restricted to the exemplary embodiment described and illustrated.

Fig. 3 shows a suitable circuit arrangement for the

Multivibrator MV. This is a multivibrator of a fairly well known type, based largely on the use of HICUT AND gates, and the effect of which is known per se. Timing arrangements T. and T "of the type that use the RC time constant are provided, which are equipped with externally actuated adjustment potentiometers VR or VR ₁ to determine the length of time during which they are wlrkaam are. The flip-flop effect of the multivibrator is obtained by cross-coupled HICHT-UKD gates G and <3_, which form a bistable trigger circuit and the gate capture signals for the timing arrangements are

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eentärausgangs the gates G ,. and G via reversing arrangements G ₁ ,,. and G_ taken. If a timing order T. or T "the end of the effective

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is reached, the change in the output signal switches the bistable Trigger circuit, which in turn causes the timing capacitor is discharged in the relevant timing order and that charging of the timing capacitor of the other 'timing arrangement is commenced.

It should _f appreciated that when the multivibrator is in state of the exhalation phase, the reception of a "0" which signal came from the inverting Reinforced A _1, the patient trigger circuit (Fig. 2) at the input of the gate Gci, causes the bistable Triggerschal tuhg lets the multivibrator tip over into the inhalation state, as mentioned above. It should also be evident that a signal on the line c_, which comes from the output of the gate G ^ _f can be used to switch on a separate inhalation timing arrangement, that a signal on the line d can be used to thereby the timing arrangement T « block that their input is held at "0" and that the output signal of the separate timing arrangement can regulate the inhalation time of the multivibrator via the line e_.

So in principle multivibrator becomes the possibility

the inhalation time of the same by means of a separate time

»To regulate the stiüiinordnung. Such a separate Zeitbestinraungsar.or tion can be applied to any part of a deep inhalation unit Unit has the deep inhalation function described above »Such a Unit will now be explained with reference to FIG. 4, with the connections this unit with the basic control circuit of the ventilator, as described with reference to FIGS. 2 and 3 by

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Ä » Ά * SL * $ L> Jg. And f are indicated in the relevant figures.

The deep inhalation unit of Fig. 4 is divided into two main parts, an additional timing arrangement for the inhalation phase thereof Shape like the timing circuit for the inhalation phase of the I-fultivibrator, and a gap timing arrangement that includes a

• #

Pulse generator (another timing arrangement) and a Split counter. The inhalation timing control unit contains a timing

j measurement arrangement T, the duration of which is determined by the Zeitkonutaiite potentiometer VR_, the input AND gate G. ,, the output reversal arrangement · C .. and an input clearance reversal arrangement _{G 1 ^.} The output signal of the reversal arrangement G .. is the back input of two bistable

• 4

Trigger circuits BS. and BS "and also supplied via the line e_ of the NICET AND gate Ο- in the reversing arrangement (FIG. 5). The output signal from output Q of the bistable arrangement BS_ is fed to the blocking input of gate G ₁₉ (Fig. 3) via line (1) and also to the blocking input of an analog gate Ο, -. This gate is of the same type as gate G. * (Fig. 2) and therefore replaces it during a deep breathing period. The gate ISsst the signal originating from the deep inhalation volume control potentiometer VTL · through to the line I »and that as long as a" 1 "signal is present at the upper input while the gate is locked, wenu an ¹¹ O "signal is present at the blocking input.

The "'Aktimpulsgenerator der Tleieinatinun £ 3zwisc.hi; nrnunzeitbestinmungsanordnung enlhilt a tent determination unit T. (corresponding to the above-Dgcnannt Zeitbeatimmungeeinheit), üie for example from 0 _t 25 to 7 seconds ii> t, a mcnostaldle arrangement' -, ι a reversal arrangement G. and an inverting amplifier, which form a closed loop. The generated pulses are generated from the Au

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the reversing arrangement G. "the input of a binary counter consisting of eight stages (ie a counter« which can count up to 256) CTR »The output signals of these eight stages are fed into a NOT-DND gate G _{? f) 1} 'which den" all-i-state ¹¹ of the counter determines (ie, the highest position before the counter is reset back to Nui the subsequent input pulse) -zusammengefügt. the output of the NAND gate G ₃₀ is reversed by die.Umkehranordnung G._ and your setting input of the bistable trigger circuit BS supplied. ■

To facilitate an explanation of how the

The clock pulse generator assumes that the mnostable trigger circuit MS is in the untriggered state, ie there is a "1" at the 5 output. This is a ^M 0 "again by the inverting amplifier A _fl in a" 1 by reversing by the reversing assembly G "vice. * - is converted, the input of the timing arrangement T supplied" 1 causes * that with the Ladjen of Timing capacitor of timing

/
Mood unit T. is started. After a period of time which is determined by the RC time constant, the timing arrangement delivers a "C" signal at the output. This signal triggers the monostable trigger circuit HSV, the triggered state of which lasts, for example, 1 millisecond "during which time the output signal at the ζ -Output ^{1 is} O ". This "Ö * is converted into an ⁿ 1 * ', which is necessary for the delivery of a clock pulse at the counter CTR and which is converted back into an eice *' 0 ⁿ _{in the inverting amplifier A n} * This" C "coil discharges the timing capacitor and afterwards When the pulse expires, the tent determination arrangement begins again with the time period. In this way, a series of clock pulses with an I-mpula duration of 1 millisecond is generated, which is fed to the input of the counter GTH. When the counter reaches the highest position

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has (in this embodiment form after 256 pulses) the ^M all-1 "condition causes the NOT-UUD gate G-. to deliver an ¹¹ O" s output, which is converted into a "1" by the reversing arrangement G. _q is converted to the setting input of the bistable trigger circuit BS. is supplied, at the Q output of which a "1" arises. This bistable trigger circuit acts as a memory in which it is stored that the counter has reached its highest position and that consequently deep inhalation is to be expected.

The deep inhalation phase must of course be in that

Begin at the moment when the multivibrator switches from the exhalation phase to the inhalation phase and consequently the deep inhalation control has to wait for this moment. In the meantime the counter is reset to KuIl and starts to count again, the ¹¹ BlIe-I "-status is over and consequently the highest counting position information must be kept until the following inhalation phase begins. The output signal" 1 "of the bistable trigger circuit BS ₁ is fed to the setting input of the bistable trigger _{circuit BS 2} , but this trigger circuit does not set itself before it receives a trigger pulse via the line £ at the T input

From an inhalation phase to an exhalation phase (FIG. 3), a "0" appears at the output of gate G ₁₀ and therefore the bistable empty circuit BS. now triggered via the line £ and delivers a "1" at its Q output and a "0" at its Q output. The ^N 1 "on the control input of the gate G ₁ - now enables the gate to receive the analog signal, which represents the required deep inhalation volume, which has been set by the potentiometer VH-, via the line b to the input of the Ye ro

same arrangement CO. (Pig. 2). The same "O ¹¹ blocks the AND gate G ₁₂ (Flg. 3) via line t> and in this way makes inhalation» -

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timing arrangement of the multivibrator ineffective »The" 1 "at the Q output of the bistable trigger circuit ES clears the gate G and the" 0 "at the ζ output blocks the analog gate G ₁ via line a (Fig. 2). This way, the adjustment potentiometer becomes VR _? Replaced for the normal gas volume by the potentiometer VR_ for the deep inhalation volume at the input of the comparison arrangement CO ₁ . The bellows are now filled with the deep inhalation volume instead of the normal volume. The "0" occurred c_ "the switchover point in time on the line is determined by the inverter circuit-C, in a" 1 "is reversed and the AND gate G will now be made free, the" 1 "at the input of Tiefeinatmungszeitbestimmungsanordnung T, has the consequence that = this begins its timing phase. After this phase, which is determined by the setting of the deep inhalation time potentiometer VR ", a" 1 "occurs at the output of the timing arrangement, which is indicated by the gate G ₁ . is reversed to a "0", what the bistable trigger circuit Br BS ₁ and BS _? resets and is fed to the multivibrator MV via line £ so that it switches to the exhalation phase »

In this way, a deep inhalation volume is periodically supplied to the patient during a deep inhalation phase, with intervals that are determined by the setting of the time constant of the Zeitbeatimmungsanordnunä ^{1 T.}

At the end of this phase, the vibrator switches back to the airing phase. This leaves ^a n dr olOnstchend described switching process in the URAG * taught ReihGnfo] f: expire c, woki the controls which n is the norr..nlf> S tenerungi η make rückgUngig be lifted KO that the S "halturiß. returns to normal work until the KZvi; -c lioriraumzählcr CTJi visier dje hi? c _}. Kto position reaches,

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BATH ORIGINAL

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ie after an interval of about 1 to 30 minutes _t depending on the setting of the time constant potentiometer VR ″.

Sometimes it is necessary to take a deep breath if requested, for example for physiotherapy to empty the lungs with the help of pressure exerted with the hands after a deep inhalation. For this purpose there is a push button which essentially supplies an output signal which corresponds to the signal which indicates the highest position of the counter CR. The actuation of the deep inhalation trigger button ST has the consequence that a "0" occurs at the input of the reversing arrangement 20, after which the effect of the circuit continues to correspond to that which has been described in relation to the periodic effect. When the button ST is released, the "Q" is reversed by the reversal arrangement f 21 and zvar into a "1" which is generated by the capacitor C _? is differentiated, so that a short "1" pulse is produced, which is fed to the reset signals of all stages of the counter. In this way the counter is reset to the counting position zero, which ensures that the entire intermediate '? space runs before deep inhalation is delivered again. This prevents the counter from being able to induce such deep inhalation again very shortly after a manual deep inhalation.

309809/0782

Claims (2)

-21- 'PHB. 32186. PATENT TO PROBLEMS ι (1 / ventilator of the time-controlled type with a prograna timer for controlling a ventilation cycle with an inhalation phase and an exhalation phase, the time periods of which are adjustable and with which Device for each inhalation phase of a ventilation cycle, a specified precisely metered amount of gas can be administered to a patient, with a gas container of variable content for measuring and temporarily storing the specified precisely measured amount of gas during an exhalation phase, as well as for expelling the precisely measured amount of gas during an inhalation phase, with a drive device for enlarging and reducing of the contents of the gas container with regard to the gas dimensions, storage and drive-out function of the same, with a "display device for displaying." the momentary size of the contents of the gas container and with setting means !: zuo setting the size of a precisely measured amount of gas, characterized in that that the display device contains a first transducer, the output signal of which is a measure of the instantaneous size of the Contents of the gas container that the setting means for setting the GrSsss the precisely measured amount of gas include a second converter, whose Ajsgangssignal in large a measure is to be precisely measured for each ventilation cycle Amount of gas that a signal output of the first converter with a first signal input and a signal output of the second convertera with a second signal input of a comparison arrangement and that a signal from even. »: the comparison arrangement is coupled to a switch for switching the drive arrangement of the gas container on and off. 2. Ventilator according to claim 1, characterized in that ia ~: the device comprises a second comparison ^{arrangement, the signal output 1 of} the first converter with a first signal passing through the comparison arrangement 309809/0782 -22- PHB. 32186. and a second signal input of the same is coupled to a signal output of an adjusting arrangement, with the aid of which an output signal is set can be that corresponds to the output signal of the first converter, if the gas container is in the state of minimal content. 3. Ventilator according to claim 2, characterized in that that the signal output of the second comparison arrangement with a first Signal input of an alarm circuit is coupled to output an alarm signal at the beginning of an exhalation phase in the event of an error, an input signal to the first signal input, with a second signal input of the alarm circuitry coupled with a signal output of the program timer. 4 · Ventilator according to claim 3 »characterized in that that the alarm circuit is a monostable trigger circuit for maintaining an alarm signal during one to be determined by the trigger circuit Contains duration. 5 · Ventilator according to one of the preceding claims, dadure characterized in that the device includes second setting means for setting the size of an exactly to be measured amount of gan, which setting means one contain a third converter, the output signal of which is a measure in terms of its size is for a quantity of gas to be measured precisely during a ventilation cycle, that it contains a time control arrangement assigned to the program timer already mentioned for maintaining an inhalation phase during a certain adjustable period of time that said second setting means and the associated tent bumper arrangement via a gate circuit are connected to the program timer and the second signal input of the first comparison arrangement, and that the gate circuit has a signal input for a priority signal, the presence of which is followed by an inhalation phase after the end of a previous exhalation phase, dtrer. 309809/0782 -23- · PHB. 32186. Duration by the assigned time control arrangement and that of the patient supplied amount of gas can be determined by setting the second setting means. 6, ventilator according to claim 5t, characterized in that; the priority signal input of the gate circuit with a clock pulse generator is coupled to a deep inhalation interval timing arrangement. 309809/0782